WO2010050170A1 - Dispositif de mesure de lumière d'un organisme - Google Patents

Dispositif de mesure de lumière d'un organisme Download PDF

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Publication number
WO2010050170A1
WO2010050170A1 PCT/JP2009/005630 JP2009005630W WO2010050170A1 WO 2010050170 A1 WO2010050170 A1 WO 2010050170A1 JP 2009005630 W JP2009005630 W JP 2009005630W WO 2010050170 A1 WO2010050170 A1 WO 2010050170A1
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Prior art keywords
light
probe
subject
probes
measurement
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PCT/JP2009/005630
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English (en)
Japanese (ja)
Inventor
舟根司
小幡亜希子
木口雅史
小泉英明
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株式会社日立製作所
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Priority to JP2010535653A priority Critical patent/JP5147949B2/ja
Publication of WO2010050170A1 publication Critical patent/WO2010050170A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6814—Head
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
    • A61B5/14553—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases specially adapted for cerebral tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/74—Details of notification to user or communication with user or patient ; user input means
    • A61B5/742—Details of notification to user or communication with user or patient ; user input means using visual displays
    • A61B5/743—Displaying an image simultaneously with additional graphical information, e.g. symbols, charts, function plots

Definitions

  • the present invention relates to a living body optical measurement device for noninvasively measuring cerebral blood dynamics.
  • the local hemodynamic changes near the surface of the human brain can be measured non-invasively by optical topography.
  • the optical topography method irradiates a subject with light having a wavelength belonging to the visible to infrared region, detects multiple signals of light that have passed through the subject with the same photodetector, and detects the amount of hemoglobin concentration change (or hemoglobin concentration). This is a method of measuring the change in the product of the optical path length) (see, for example, Patent Document 1).
  • brain function measurement techniques such as MRI and PET, it has a feature of low restraint on subjects. In clinical settings, language functions and visual functions are measured.
  • the orbital frontal cortex (orbitofrontal cortex) and the limbic system especially in fMRI, have cavities such as the nasal cavity and frontal sinus in the human head. In some cases, false measurements could not be detected due to the change, making it impossible to measure accurately.
  • the signal is a T2 star (T2 * ) weighted signal, and the difference in permeability at the boundary of permeability (or magnetic susceptibility) such as nasal cavity, sinus cavity, ear cavity, tissue / air or tissue / fat May cause distortion of the local magnetic field, resulting in signal degradation and signal position error due to spin phase dispersion, that is, artifacts (false images).
  • the optical fiber is inserted into the nasal cavity or the light is irradiated from outside the nasal cavity, between the eyebrows or from the forehead, the light irradiation position is closer to the eyeball than the conventional optical topography method.
  • it is necessary to strengthen safety measures to prevent eye damage caused by light or a probe.
  • An object of the present invention is to provide a technique for solving the above problems.
  • the living body optical measuring device of the present invention comprises a light irradiation / light receiving probe and a probe holding unit for holding these probes in order to irradiate light to the brain bottom stably with good reproducibility.
  • a nose pad installed on the probe holder.
  • the light irradiation probe is installed so that light is irradiated approximately vertically between the eyebrows, and light is irradiated after the probe holder is fixed to the living body via the nose pad so that the light does not enter the eyeball of the subject. It has a mechanism that starts irradiation of light from the probe toward the living body. It also has a mechanism for preventing the probe from hitting the eyeball.
  • the light receiving probe is placed between the eyebrows or on the forehead and receives light that has been transmitted and scattered through the bottom of the brain.
  • the light irradiation probe has an angle adjustment mechanism, and can irradiate light in an optimal irradiation direction that differs for each subject.
  • the light receiving probe has a similar angle adjustment function.
  • the present invention it is possible to stably irradiate light to the deep part and the bottom part of the brain with good reproducibility.
  • the ability to measure changes in blood dynamics in the limbic system, orbital frontal cortex, pituitary gland, thalamus, and hypothalamus at the bottom of the brain enables the acquisition of biological information that could not be obtained with conventional optical brain functional imaging technology become.
  • the apparatus block diagram of this invention The apparatus block diagram which has a mechanical switch as a contact sensor. Control mechanism for limiting probe protrusion. Probe length adjustment mechanism. The block diagram at the time of holding band use.
  • the apparatus block diagram when performing extranasal light irradiation and the light detection from a forehead The apparatus block diagram when performing intranasal light irradiation and the light detection from a forehead.
  • Probe angle setting screen The flowchart at the time of a probe angle setting.
  • the apparatus block diagram which has a visual stimulus presentation part.
  • FIG. 1 shows an apparatus configuration diagram of the present invention.
  • a probe holder 102 for holding the light irradiation probe 104 and the light receiving probes 103 a to 103 c is attached or fixed to the subject 10 via the nose pad 101 and the ear hook 105.
  • the reproducibility of the positions of the light irradiation probe 104 and the light receiving probe 103 with respect to the subject 10 is maintained. That is, even if the attachment / detachment is repeated, the positions of the light irradiation probe 104 and the light receiving probe 103 at the time of attachment are substantially the same on the subject 10.
  • the light irradiation probe 104 and the light receiving probes 103a to 103c are optically connected to the light source 201 and the photodetectors 202a to 202c through optical fibers 301a to 301d.
  • the light source 201 and the light detector 202 are electrically connected to the apparatus main body 20, and the apparatus main body 20 includes a control unit (not shown) therein.
  • the control unit includes an analog-to-digital converter for analog-to-digital conversion of an analog signal photoelectrically converted by the photodetector, and a calculation unit for calculating and analyzing the biological information of the subject from the output of the analog-to-digital converter.
  • a storage unit for recording the biological light measurement program and information necessary for the processing and temporarily storing the acquired data and the calculation result, controlling the irradiation timing of the light source 201, and the photodetector 202.
  • the measurement result obtained by the calculation is displayed on the display unit 30, and stimulation for the subject 10 is performed by the stimulus presentation unit 40.
  • the display unit 30 and the stimulus presentation unit 40 are calculated or controlled by the control unit of the apparatus body 20.
  • the display screen of the display unit 30 also has a part of the function of input means for the apparatus main body 20.
  • the light irradiation probe 104 and the light receiving probe 103 are in contact with or close to contact with the subject 10 at the time of measurement, projecting from the probe holding unit 102, and placing the probe close to the eyeball When doing so, it is necessary to take measures not to poke the eyeball. For this reason, the light irradiation probe 104 and the light receiving probe 103 are provided with a safety mechanism that can only be protruded after the probe holder 102 is attached to the subject 10. Whether or not the probe holder 102 is set on the subject 10 is detected by the contact sensor in FIG.
  • a mechanical switch 401 (401a to 401c) is used, and is configured to be turned on when in contact.
  • the mechanical switch 401 is provided at a plurality of locations on the probe holding unit 102, and is controlled so that the probe cannot be projected unless all the switches are completely turned on.
  • a small micro switch or the like may be used.
  • a pressure sensor or an optical sensor may be used as the contact state sensor.
  • electrical wiring may be passed over the probe holding unit 102, or wireless communication or the like may be used. The contact sensor information is transmitted to the control unit of the apparatus main body 20 or the light irradiation probe 104 / light receiving probe 103.
  • Fig. 3 shows an example of the control mechanism for limiting probe protrusion.
  • the protrusion length of the probe 111 can be adjusted by attaching a key-shaped unevenness to the outside of the probe 111 and the inside of the probe support member 112 as shown in FIG.
  • the structure is pushed in against the repulsive force of the compression spring 113.
  • the mechanical switch 401 is turned OFF, the probe support member 112 is electromagnetically removed, and the probe 111 is pulled back again by the force of the compression spring 113.
  • the mechanical switch 401 is turned off (non-contact state)
  • the mechanical switch 401 is turned OFF, laser irradiation is stopped even during measurement, and laser light can be prevented from entering the eyeball of the subject 10 unintentionally. Can keep. That is, the mechanical switch 401 is also used for stopping laser irradiation in an emergency.
  • the opening / closing control of the probe support member 112 has been described on the assumption that it is performed by an electromagnetic switch using an electromagnet or the like. It is also possible to control so that 112 is opened and closed by the electromagnetic switch only when the mechanical switch 401 is in the ON state.
  • FIG. 4 shows an example of the probe length adjustment mechanism.
  • the optical fiber 301 is fixed inside the bolt-shaped probe 121, and light can be irradiated and received from the tip of the bolt-shaped probe 121.
  • a male screw is cut outside the bolt-shaped probe 121, and a female screw is cut inside the nut-shaped knob 122.
  • the bolt-shaped probe 121 is inserted into the nut-shaped knob 122, and the probe holding portion 102.
  • a through hole is formed at a place where the bolt-shaped probe 121 penetrates.
  • the protruding length of the bolt-shaped probe 121 can be controlled by rotating the nut-shaped knob 122.
  • the nut-shaped knob 122 is pressed by the nut pressing member 123 so that the position of the nut-shaped knob 122 does not change relative to the probe holding portion 102.
  • the protruding length adjustment may be performed by fixing the nut-shaped knob and rotating the bolt-shaped probe 121. good. However, in that case, the entire optical fiber rotates, so it is necessary to consider the effect of twisting on the optical fiber.
  • the electromagnetic switch described in FIG. 3 is combined, and for example, the nut-like knob 122 is disassembled by cutting or the like, and the opening diameter is changed by the electromagnetic switch as in the probe support member 112 in FIG.
  • the same safety mechanism as in FIG. 3 can be realized.
  • the probe holding portion 102 can take various shapes including a frame type as shown in FIG. FIG. 5 shows a configuration having the holding band 131.
  • a holding band 131 is connected to or integrated with the probe holding unit 102 and fixed to the subject 10.
  • various types such as a goggle type, a sun visor type, and a mask type are possible, and equivalent measurements can be performed.
  • FIG. 6 shows a flowchart from probe setting to laser irradiation.
  • the probe holder 102 is attached to the subject 10 (the mechanical switch 401 is turned on).
  • the light irradiation probe 104 and the light receiving probe 103 are pushed in, brought into contact with the subject 10 and fixed.
  • Laser irradiation is started.
  • FIG. 7 shows a flowchart of laser irradiation control after the start of laser irradiation.
  • S701 Start of laser irradiation.
  • S702 Judgment whether the probe mounting sensor is ON (mechanical switch 401 is ON).
  • S703 Judgment whether the measurement is completed.
  • S704 At the end of measurement (when a measurement end command is received) or when the probe mounting sensor is turned off (the probe is detached from the subject 10), the laser irradiation ends.
  • FIG. 1 a schematic diagram of the probe placement and measurement position is shown in FIG.
  • One light source 201 (including three wavelengths) is provided, and the light irradiation probe 104 is disposed between the eyebrows, and is connected by an optical fiber therebetween.
  • a total of three light receiving probes 103 are arranged several millimeters above the left and right eyebrows and below the center of the forehead, and are optically connected to the photodetector 202 by an optical fiber.
  • a laser diode with three wavelengths of 678, 750, and 830 nm was used as the light source.
  • Subject 10 was a healthy woman.
  • the task needs to be a task that induces emotional changes as a stimulus to activate the orbital frontal cortex. It is known that the orbital frontal cortex is related to the emotional system and reward system (see Rolls, Brain Cogn., 2004, Non-Patent Document 2).
  • FIG. 9 shows the location of the orbital frontal area located at the base of the brain.
  • FIG. 9 shows an example of incident / detection positions of incident light 501 and detection light 502 for measuring the brain base 500 with light.
  • the experiment described here is a configuration in which light is incident from between the eyebrows and the light is detected from the forehead.
  • the authors' task is to display food on a display, see it, photographs, especially to see past photographs related to the subject 10, and mental arithmetic. Changes in hemodynamics were measured.
  • the measurement principle of hemodynamic change is a method of calculating the amount of change in the product of hemoglobin concentration and optical path length (here, this is defined as hemoglobin concentration length change) using multiple wavelengths around 800 nm. Using.
  • the analysis method of the hemodynamic change is described in detail in Patent Document 1, Non-Patent Document 1, and the like.
  • a past photograph related to the subject 10 such as a human face photograph was taken as a subject.
  • channel 2 (ch2) in the probe arrangement of FIG. 8 is shown in FIG. A total of 40 seconds of 15 seconds (landscape photo), 10 seconds (face photo), and 15 seconds (landscape photo) was taken as one block, and this was repeated 10 blocks, and the averaging process was performed.
  • the oxygenated hemoglobin concentration length change (oxy-Hb) increases during the task period in which the facial photograph is presented, and the deoxygenated hemoglobin concentration length change (deoxy-Hb) also slightly increases. Since the subject of photography is thought to affect the emotion of the subject 10, it is expected that the orbital frontal area located at the base of the brain is activated. Therefore, a part of the signal obtained in FIG. 10 is considered to be derived from the orbital front.
  • the orbital forehead is located in 11 areas of Broadman in the prefrontal area, behind 10 areas of Broadman, so when light is applied to the orbital frontal area from the scalp or between the eyebrows
  • 10 fields of Broadman have a working memory integration function. Number memory, 2. Language tasks, 3.
  • FIG. 11 is a flowchart of a method for separating signals from a plurality of brain regions (Broadman's 11 fields (orbital frontal field), 10 fields (frontal pole), 46 fields (frontal dorsolateral part), etc.)). Indicates.
  • this flow when the overlap signal from two brain regions at each measurement point is separated, if the signal of one brain region has already been separately measured separately, each measurement point of the other signal is measured. The distribution in is separated.
  • the signal separation method will be described in detail below.
  • a plurality of brain regions to be separated are selected. These brain parts are set, for example, as A region: frontal pole and B region: orbital frontal area.
  • (S1102) A measurement point (light source / detector pair) is placed near the A area and the B area, and the measurement points are set to ch1, ch2,. The signals obtained from these measurement points are assumed to be dominated by signals from the A region and / or the B region. In other words, the signal change at each measurement point due to activation of other areas is ignored.
  • (S1103) A task for mainly activating the area A is performed and measurement is performed (task ⁇ ). For example, a branching task for performing calculations during storage is performed. At this time, data obtained at the measurement point ch1 when task ⁇ is executed is expressed as D (ch1, ⁇ ) or the like.
  • (S1104) A control task that does not activate area A is performed (task ⁇ ').
  • the difference (D (ch1, ⁇ ) ⁇ D (ch1, ⁇ ′)) and the like are calculated and set as the activity value of the area A at the measurement point ch1.
  • the activity value (A (ch1), A (ch2),...) Of area A at each measurement point is calculated.
  • the activity value distribution of the A area at each measurement point is displayed with a numerical value or a color.
  • the first task (task ⁇ 1) that mainly activates the B region is caused to perform measurement.
  • the visual task is a photograph of a friend or family member of the subject 10.
  • a second task (task ⁇ 2) that mainly activates the B region is caused to perform measurement.
  • task ⁇ 2 A second task (task ⁇ 2) that mainly activates the B region is caused to perform measurement.
  • the subject 10 has a visual task with a photograph of a favorite food.
  • S1109 The following simultaneous equations are calculated, and variables B (ch1), B (ch2), B (ch3), ka ( ⁇ 1), ka ( ⁇ 2), kb ( ⁇ 1), kb ( ⁇ 2) are obtained (measurement) When the point is 3 points). When the number of measurement points is 4 or more, obtain by the least square method.
  • D (ch1, ⁇ 1) ka ( ⁇ 1) ⁇ A (ch1) + kb ( ⁇ 1) ⁇ B (ch1)
  • D (ch2, ⁇ 1) ka ( ⁇ 1) ⁇ A (ch2) + kb ( ⁇ 1) ⁇ B (ch2) Formula 3.
  • D (ch3, ⁇ 1) ka ( ⁇ 1) ⁇ A (ch3) + kb ( ⁇ 1) ⁇ B (ch3) Formula 4.
  • D (ch1, ⁇ 2) ka ( ⁇ 2) ⁇ A (ch1) + kb ( ⁇ 2) ⁇ B (ch1) Formula 5.
  • D (ch2, ⁇ 2) ka ( ⁇ 2) x A (ch2) + kb ( ⁇ 2) x B (ch2) Formula 6.
  • D (ch3, ⁇ 2) ka ( ⁇ 2) x A (ch3) + kb ( ⁇ 2) x B (ch3) Formula 7.
  • kb ( ⁇ 1) 1
  • D is the measured value
  • A is the activity value of the A area obtained in (S1105). Since the equation is 7 for variable 7, the variable can be obtained.
  • the difference between the average values of oxy-Hb during the stimulation period and during the non-stimulation period may be used as the calculation method of the measurement value.
  • the task A1 and task ⁇ 2 are considered to be active in the A region, and the contribution of the activity to the signal is unknown, but the contribution rate of the signal change to each measurement point is considered to remain the same for each task. Therefore, by using the A area activity value obtained in (S1105) as the contribution rate from each area of the brain to a specific measurement point, the influence of the A area activity is eliminated, and the B area activity at each measurement point. The value can be determined. In order to determine the coefficients ka and kb and the activity value of the B region, two or more tasks for activating the B region are required, and three or more measurement points are required. Here, it is assumed that the B region active in task ⁇ 1 and task ⁇ 2 is the same region.
  • signals from two or more brain regions may be separately measured using principal component analysis or independent component analysis.
  • the orbital frontal area known to be related to the emotional system and reward system can be measured non-invasively, it can be used to monitor human emotional changes. It can be applied and contributes to the elucidation of emotional and reward functions in the human cerebral cortex, which is very meaningful.
  • the activity of the orbital frontal region in the gustatory task is measured, and the change in the mood state of the driver is monitored by an attempt to measure the preference from the signal change and the measurement during driving of the passenger car.
  • It can be used for various feedbacks to the driver according to the state.
  • it can be used for the driver to call attention when the mood is unstable, to limit the speed in an irritated state, or to determine the mood state in combination with vehicle speed / acceleration information. is there.
  • hypothalamus can be measured in the brain base, the hypothalamus is the center of human instinctive behavior including sleep. By measuring the hemodynamic changes around the hypothalamus during sleep, Can contribute to the elucidation of activities. In addition, because the hypothalamus regulates sympathetic and parasympathetic functions, these abnormalities may be detected early. Furthermore, the ability to measure the pituitary gland, which is an endocrine organ that secretes many hormones, is thought to be helpful in diagnosing diseases related to these hormone secretions.
  • this apparatus may be configured to be installed in eyeglasses worn by the subject.
  • the nose pad 101 of the present apparatus can be omitted.
  • the present apparatus is configured to have a spectacle connecting portion for fixing to the spectacles instead of the nose pad 101.
  • the glasses worn by the subject have been described here, the glasses are not limited to glasses and may be goggles.
  • the optical fiber 301 is eliminated, and the apparatus main body 20, the light source 201, and the photodetector 202 shown in FIG. is there.
  • the light source 201 and the photodetector 202 in the wireless control device 151 are directly connected to the light irradiation probe 104 and the direct light receiving probe 103, respectively.
  • the wireless control device 151 includes a wireless device, a circuit for driving the light source 201, an amplifier for amplifying the photocurrent from the photodetector 202 and converting it into a voltage, an analog-digital conversion circuit, and a battery. Yes. Data can be transmitted from the wireless control device 151 to the remote control device 150 wirelessly.
  • the remote control device 150 may be a computer having a wireless device, and may include a display that displays obtained data and information of the subject 10. By using wireless, the restraint of movement on the subject 10 is reduced, and measurement in a more natural state is possible. In addition, the optical fiber 301 does not block the field of view of the subject 10, and it is possible to give a visual stimulus to the subject 10 without narrowing the field of view of the subject 10.
  • FIG. 13 shows a configuration in which the eyeball is protected by the eyeball protection plate 191 in the living body light measurement apparatus of the first embodiment until just before the start of measurement.
  • the eye protection plate 191 is a slide type filter. This is to prevent the light from the light irradiation probe and the light irradiation probe / light receiving probe from hitting the eyeball.
  • the eye protection plate 191 is slidable and can be removed. After the probe set is completed, the eye protection plate 191 can be removed, and measurement can be started after adjusting the probe length.
  • a flowchart showing the procedure for using the eye protection plate 191 is shown in FIG. (S1401)
  • the probe holder 102 is attached to the subject 10 (the mechanical switch 401 is turned on).
  • the eye protection plate 191 is slid and removed.
  • the light irradiation probe 104 and the light receiving probe 103 are pushed in and brought into contact with the subject 10 and fixed.
  • Laser irradiation is started. Note that a part or all of this flow may be automatically performed.
  • the sliding-type opening / closing operation of the eyeball protection plate 191 can be realized using an electromagnetic switch or the like that responds to ON / OFF of the mechanical switch 401.
  • the probe pushing in (S1403) it is possible to adopt a configuration in which the probe protrudes only by the spring force by shrinking the spring or the like with a weak force in advance. Laser irradiation can also be realized using electromagnetic switches.
  • FIG. 15 illustrates that the light is irradiated into the nasal cavity through the nostril to measure the brain bottom, and the nasal cavity directly below the brain bottom.
  • light is directly applied to the inner mucous membrane.
  • the light can be detected from between the eyebrows, the forehead, or under the nostrils of the subject 10.
  • FIG. 15 shows an example in which light is emitted from the nasal cavity toward the nostril and light detection is performed from the forehead.
  • the optical fiber 301 and the light irradiation probe 104 may be inserted into the nasal cavity as shown in FIG.
  • the light receiving probe 103 or the light receiving optical fiber 301 is also inserted from the same nostril or the other nostril on the left and right sides, so that light can be irradiated and detected only by being inserted into the nose as shown in FIG. You can also. 15 to 17, it is possible to irradiate the orbital frontal cortex (11 fields of Broadman) with high accuracy by directly irradiating the intranasal mucosa just below the brain bottom.
  • the advantage of this method is that it is less susceptible to the activity of other brain regions (e.g., frontal poles (10 broadman fields) and dorsolateral prefrontal areas (46 broadman fields)).
  • a probe angle adjustment mechanism 161 is provided to control the direction of the light irradiation probe or the light receiving probe.
  • the probe angle can be manually adjusted by providing a rotation mechanism and fixing with a screw or the like. Thereby, it becomes possible to set the optimal light irradiation angle or light receiving angle for each subject. Since the light irradiation probe and the light receiving probe are held by the probe holding unit 102 and the probe holding unit 102 is fixed to the subject 10 via the nose pad 101, it is possible to perform stable measurement and measure again. The reproducibility is maintained even when doing so.
  • a lens for narrowing the beam divergence angle may be provided at the tip of the probe in order to suppress the spread of the light from the optical fiber 301 to be less than the diameter of the nostril.
  • the incident angle of light becomes important.
  • the incident direction is closer to the front side (facial surface side)
  • the light passes through the surface of the face and is not absorbed by the tissue so much. growing.
  • the hemoglobin signal intensity is considered to be small. That is, it does not mean that the light detection intensity is high.
  • the incident direction is closer to the back of the head, the light is incident on the deep brain, and the amount of light detected between the eyebrows or the forehead is small.
  • the amplitude of blood volume fluctuation due to brain activity is expected to increase, but the detected light quantity decreases, so the signal-to-noise ratio (S / N ratio) decreases. Therefore, when light enters the nasal cavity through the nostril, there is an optimum angle for measuring the brain base in terms of the S / N ratio.
  • the angle varies depending on the site where hemodynamic changes are to be measured. For example, it is expected that there will be a difference between 11 fields in Broadman and 46 fields in Broadman. Therefore, it is necessary to determine the optimum angle by the apparatus body 20 and set the probe angle to the angle by the probe angle adjustment mechanism 161. Therefore, for example, the probe angle is set as follows.
  • an optimization (maximization) parameter is selected with a radio button 1801.
  • “detected light quantity” or “hemoglobin (Hb) signal intensity” can be selected.
  • “detected light amount (Light amplitude)” is selected.
  • use data is selected with a radio button 1802.
  • “Measure from now” or “Read from database” can be selected.
  • “measurement from now” is selected.
  • the probe angles are set manually or automatically in order, and a “measure” button 1805 is pressed. After the measurement, the measured value 1803 for each channel is displayed on the screen.
  • a “remeasurement” button 1804 When remeasurement is performed, a “remeasurement” button 1804 is pressed. For each measurement, an optimization function is calculated in consideration of the optimization parameter, and an optimum angle determination result is displayed on the optimum angle determination result display unit 1806.
  • a “save” button 1807 When the measurement of the candidate probe angle is completed and the result is stored, a “save” button 1807 is pressed, and when the angle setting is ended as it is, an “OK” button 1808 is pressed.
  • “Read from database” is selected with the radio button 1802, the measured values of each channel can be obtained by reading the past measurement result of the subject to be measured or by reading the average value in the same age group.
  • the evaluation function is calculated based on the optimization parameter displayed and selected with the radio button 1801, and the result of the optimum angle is displayed on the result display unit 1806.
  • the evaluation function here, for example, an average value of all measurement channels may be used. Also, a weighted sum corresponding to a brain region to be measured with priority in each measurement channel may be used.
  • FIG. 19 shows a flowchart when setting the probe angle.
  • An optimization parameter is selected (for example, “detection intensity”, “orbital frontal field Hb signal intensity”, etc.).
  • S1902 Use data is selected (for example, “measure from now”, “read from database”, etc.).
  • S1903 When “Read from database” is selected, the database is read,
  • S1904 When “measurement from now” is selected, an initial value of the angle of the probe for irradiation / light reception is set.
  • Measurement is performed (for example, the task for the orbital frontal area and the task for the frontal pole are performed together and detected at a plurality of sites).
  • a signal for example, orbital frontal area activity) is extracted.
  • the hypothalamus regulates sympathetic nerve function, parasympathetic nerve function, and endocrine function, and is also known to be the center of instinct behavior such as eating and drinking behavior, sleep, and emotional behavior such as anger and anxiety. If biometric information from the hypothalamus can be stably obtained by the present invention, it becomes possible to diagnose diseases related to these functions, measure changes due to aging, and the like.
  • the pituitary gland also regulates endocrine function, and it is known that hypopituitar function causes growth hormone deficiency and thyroid stimulating hormone deficiency, and pituitary tumors press the optic nerve in the brain to reduce vision ⁇ It is known that visual field disturbances and pressure on the hypothalamus can cause mental and consciousness disorders. If it is possible to measure hemodynamic fluctuations in the pituitary gland and monitor it over time according to the present invention, it becomes possible to make early diagnosis of various diseases associated with pituitary function decline. This technique can also be used to monitor hemodynamic changes in the hypothalamus and pituitary gland during surgery.
  • an optical system such as one or a plurality of concentrators is provided in the nasal cavity or outside the nasal cavity to receive light from a specific location on the intranasal mucosa and receive light from the specific location. It is good also as a structure which enables.
  • the angle dependence can be reduced without adjusting the angle. It is thought that few measurements are possible.
  • an observation endoscope or an image fiber may be simultaneously inserted into the nasal cavity to monitor the nasal cavity.
  • the biological light measurement device includes a probe or an image fiber having an endoscope function, so that high accuracy of the light irradiation / detection position can be realized. Since the probe or image fiber having an endoscope function is fixed to the probe holding unit 102 and is stably fixed to the subject 10 by the effect of the nose pad 101, the burden on the doctor who is an operator can be reduced. The position and angle of the light irradiation / light receiving probe can be finely adjusted directly by the robot arm for endoscopic surgery.
  • FIG. 20 illustrates a case where the probe holding unit 102 has a spectacle frame shape having a nose pad and an ear hook.
  • a visual stimulus presentation display 171 is provided in front of the eyeball, and the visual activity is presented to the subject 10 and simultaneously the brain activity of the subject 10 is measured.
  • the auditory stimulus presentation earphone 181 presents the auditory stimulus to the subject 10 and simultaneously measures the brain activity of the subject 10.
  • Other stimulus presenting means may be provided.
  • brain activity it is often necessary to present stimuli.
  • By connecting to a device efficient measurement is possible.
  • the visual stimulus presentation display covers the front of the eyeball, it is possible to eliminate most of the effects of other visual stimuli. That is, the viewing angle of the stimulus presenting unit for the subject 10 can be increased.
  • the subject 10 is normally restricted in movement during the presentation of the visual stimulus in the measurement.
  • this visual stimulus presentation device is fixed relatively stably with respect to the subject 10, so that the subject 10 may move and the visual control. There is no need for special maintenance of the surrounding environment. Therefore, when the probe holding unit 102 of the apparatus of the present invention has the visual stimulus presentation display 171, it is possible to make the brain function measurement more efficient and perform measurement with higher reproducibility.
  • an optical fiber 301 connected to the light emitting probe 104 and the light receiving probe 103 is placed along the probe holding unit 102 from the rear side of the head of the subject 10 to the light source 201 or light. It can be connected to the detector 202 or the apparatus main body 20. Alternatively, a visual obstacle to the subject 10 can be removed by using a wireless system as described in the second embodiment.
  • This example relates to how to display measurement results in Examples 1 to 5.
  • Some changes in the signal at the base of the brain, especially the orbital frontal cortex, are thought to reflect emotional changes. Therefore, by displaying the activity value of the orbital frontal area, for example, the moving average value of the oxygenated hemoglobin concentration length change amount, it is possible to monitor the fluctuation of the emotion in real time. Furthermore, by predicting the type of emotion from the task to be caused by the subject 10, it becomes possible to know what kind of emotion the subject 10 has when the blood dynamic fluctuation in the orbital frontal area is large. For example, the emotional index in response to the task of showing food or smelling food represents the magnitude of emotional changes related to appetite or taste.
  • the emotional index for the task of showing a photograph of a person's face is considered to reflect the strength of the impression of the person, the presence or absence of favor or malice, and the like.
  • the emotional index when stress such as computational load is applied is considered to be emotional change due to stress caused by computational load.
  • there are three measurement points (ch1, ⁇ ⁇ ch2, ch3), and an example of a monitor screen of each signal variation on the display unit 30 when the signal from the frontal pole and the signal from the frontal orbital field are separated is shown in FIG. 21. In FIG.
  • the causes of emotional changes here, Sweetness
  • the names of areas A (2102) and B (2103), which are brain areas to be signal-separated, are the frontopolar area ), Orbitofrontal area.
  • the graph on the right side of FIG. 21 shows raw data (2108), and the raw data waveform (2109) at each measurement point is displayed together with the stimulus presentation period (2110).
  • the left side of FIG. 21 shows data (2104) obtained by separating signals derived from each brain region.
  • the A region activity value at each measurement point at a certain time is displayed in shades of color, and the value at each measurement point is displayed in a color obtained by linear interpolation (2105).
  • the B region activity value at each measurement point at a certain time is displayed in shades of color, and the value at each measurement point is displayed in a color obtained by linear interpolation ( 2106).
  • the correspondence between each color and the activity value is shown in the color bar (2107).
  • the activity value of the region B here, the orbitofrontal cortex
  • the change in the region B can be seen when it is desired to see the emotional change.
  • a signal is obtained as a haemodynamic change of the signal changes of multiple brain regions. Therefore, it is necessary to display the activity values separately for each region in this way. , It is very important in examining the effects on specific brain regions.
  • the stimulus itself can be evaluated by giving the subject 10 a stimulus that cannot be predicted what kind of brain activity appears and separating the response signal into signals derived from each brain region.
  • the signal derived from each brain region when the subject 10 uses the product 10 is a signal that reflects the feeling of the subject 10 regarding the use of the product, and thus can be used for evaluating the product.
  • the biological optical measurement device of the present invention when used simultaneously with an optical topography device (for example, Patent Document 1) for measuring the surface layer of the brain, or the biological optical measurement device of the present invention is connected to the brain.
  • an optical topography device for example, Patent Document 1
  • a light source, a light detector, a light irradiation probe, a light receiving probe and the like having a function of a head-mounted optical topography for measuring the brain surface layer part are further provided in addition to the probe for measuring the bottom part.
  • FIG. 22 shows a configuration diagram when simultaneously measuring the brain bottom and other brain surface layers.
  • the “brain surface layer” described here refers to the frontal lobe, temporal lobe, parietal lobe, occipital lobe and the like other than the brain bottom.
  • FIG. 23 shows a selection diagram of measurement parts when measuring the brain surface layer part or the brain bottom part. As shown in Example 1, when extracting the activity of the brain base, it is necessary to separate the activity from the vicinity of the frontal pole (10 areas of Broadman). Will be measured. In FIG. 23, it is possible to select one or both of the brain surface layer part and the brain bottom part on the display screen of the display unit 30 via the input means.
  • the display unit 30 in FIG. 22 displays the time series measurement data of the brain base (orbital frontal area, etc.) and the time series measurement data of other brain surface layer parts at the same time.
  • the display is controlled by the control unit.
  • FIG. 24 shows an example of simultaneous display of the bottom of the brain and other brain surface layers.
  • brain surface layer data (2401) in the left and right temporal regions, frontal pole extraction data (2402), and orbital frontal cortex extraction data (2403) are simultaneously displayed.
  • the color bar (2404) the change in the concentration length of oxygenated hemoglobin in each measurement channel is represented by black and white shading.
  • a display control method may be adopted in which acquired time-series data is arranged in the order of measurement channels, or spline interpolation is performed between measurement point data by the control unit based on position information of the measurement points. It is possible to display a two-dimensional map by performing the above-described processing, and it is also possible to display a three-dimensional solid. These data may be projected and displayed on measurement data including image data by MRI, X-ray CT or the like, or average data of a plurality of human MRI and X-ray CT data.
  • FIG. 25 shows an example in which the internal changes of the subject are reflected in the brain function measurement display.
  • This is an example of simultaneous measurement of the visual cortex and the orbital frontal cortex.
  • the horizontal axis of the graph is time [sec], and the vertical axis is the oxygenated hemoglobin concentration length change [mM ⁇ mm].
  • Representative measurement point data (2501) of the visual cortex and representative measurement point data (2502) of the orbital frontal area are displayed.
  • the calculation result (2503) calculated by the control unit using these data can be displayed on the same screen.
  • the first derivative of the data obtained by measuring the orbital frontal cortex is obtained, and that value is used as an evaluation value of the subject's internal change.
  • the first derivative of the orbital frontal cortex is positive (or, for example, 0.1 or more) Is used to display the measurement data of the visual cortex using a thick black line and a thick white line when the first derivative is negative (or less than -0.1, for example).
  • the waveform matches the measurement data of the visual cortex displayed on the top graph.
  • This display makes it possible to grasp changes (internal changes) in the emotion, concentration, motivation, etc. of the subject at each time when the visual cortex is measured.
  • visual cortex data in a state without a thick line (when the first derivative is 0 or close to 0, that is, when the internal change is small), the visual cortex data is not affected by the internal change. It is data.
  • By controlling to bring about a visual change (color coding, etc.) in this way it becomes easier to grasp changes (internal changes) in the subject's emotion, concentration, motivation, and the like.
  • the control unit determines that the data includes a large amount of the influence of the internal change when the primary differential value is equal to or greater than a predetermined threshold, and determines the influence of the internal change. It can be said that a lot of data is removed. Even if this calculation method is not used, the effect of the internal changes of the subject on the blood dynamics in the brain surface layer can be evaluated by displaying the calculation results such as simply subtracting orbital frontal cortex data. You may be able to do it.
  • an example of the visual cortex is shown, but other brain surface layers may be used.
  • the subjective mood state during measurement was grasped by conducting a questionnaire to the subjects before or after the brain function measurement, but the fluctuation of the mood state at each time could not be grasped.
  • the present invention it is possible to monitor emotional changes during brain function measurement in the surface layer of the brain in real time, and it is possible to measure brain function more accurately after grasping the change in the mood state of the subject. It becomes.
  • hemodynamic fluctuations in the surface layer of the brain are affected by the internal changes of the subject, but in reality, internal changes such as emotions and motivations and fluctuations in cerebral hemodynamics are assumed.
  • internal changes in the subject such as increased or decreased motivation, depending on the type of task to be given to the subject and the magnitude of the load.
  • Tasks performed by the subject stimulations presented to the subject by performing correlation analysis using the first derivative of the brain bottom data or brain surface data and brain surface layer data, analysis of the phase difference of each signal, etc. in the control unit ) And emotional changes can be visually displayed and evaluated.
  • a brain blood volume measurement device using light it becomes possible to stably irradiate light to the deep brain / bottom with good reproducibility, and the deep brain / bottom brain reflecting human emotional changes and the like. Changes in blood volume can be measured.
  • Subject 20 Device main body 30: Display unit 40: Stimulus presentation unit 101: Nose pad 102: Probe holding units 103a to 103c: Light receiving probe 104: Light irradiation probe 105: Ear hook 111: Probe 112: Probe support member 113: Compression spring 121: Bolt-shaped probe 122: Nut-shaped knob 123: Nut holding member 131: Holding band 150: Remote control device 151: Wireless control device 161: Probe angle adjustment mechanism 171: Visual stimulus presentation display 181: Auditory stimulus presentation Earphone 191: Eye protection plate 201: Light sources 202a to 202c: Photo detectors 301a to 301d: Optical fibers 401a to 401c: Mechanical switches (contact sensors) 500: Brain floor 501: Incident light 502: Detection light 1801: Radio button 1802: Radio button 1803: Measurement value 1804 in each channel: “Re-measurement” button 1805: “Measurement” button 1806: Optimal angle determination result

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Abstract

La présente invention concerne un dispositif de mesure de lumière d'un organisme caractérisé en ce qu'il inclut les éléments suivants : une sonde de projection de lumière ; une sonde de réception de lumière ; un support de sonde destiné à tenir les sondes ; et une plaquette prévue sur le support de sonde de manière à éclairer la région profonde/basse du cerveau d'un être humain étant stable avec une bonne reproductibilité. La sonde de projection de lumière est placée de telle sorte que la glabelle soit éclairée par la lumière depuis une direction approximativement perpendiculaire. Le support de sonde possède un mécanisme tel qu'après la fixation du support de sonde à l'organisme au moyen de la plaquette de manière à ce qu'aucune lumière n'entre dans les globes oculaires du sujet, l'éclairage de l'organisme avec la lumière provenant de la sonde de projection de lumière débute. Le support de sonde possède également un mécanisme destiné à empêcher les sondes d'enfoncer les globes oculaires.
PCT/JP2009/005630 2008-10-30 2009-10-26 Dispositif de mesure de lumière d'un organisme WO2010050170A1 (fr)

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WO2010150751A1 (fr) * 2009-06-24 2010-12-29 株式会社日立製作所 Dispositif d'instrumentation biologique
JP2013146410A (ja) * 2012-01-20 2013-08-01 Hitachi Ltd 気分評価システム
WO2013161070A1 (fr) * 2012-04-27 2013-10-31 株式会社日立国際電気エンジニアリング Outil de protection contre la lumière pour mesurer la circulation sanguine dans la tête, et procédé de contrôle et dispositif de contrôle pour installer celui-ci
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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2010150751A1 (fr) * 2009-06-24 2010-12-29 株式会社日立製作所 Dispositif d'instrumentation biologique
JP5202736B2 (ja) * 2009-06-24 2013-06-05 株式会社日立製作所 生体計測装置
JP2013146410A (ja) * 2012-01-20 2013-08-01 Hitachi Ltd 気分評価システム
WO2013161070A1 (fr) * 2012-04-27 2013-10-31 株式会社日立国際電気エンジニアリング Outil de protection contre la lumière pour mesurer la circulation sanguine dans la tête, et procédé de contrôle et dispositif de contrôle pour installer celui-ci
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CN109654393A (zh) * 2017-01-11 2019-04-19 哈尔滨理工大学 第二遮挡板和具有第二遮挡板的鼻孔照明装置
CN109654393B (zh) * 2017-01-11 2020-06-19 哈尔滨理工大学 具有第二遮挡板的鼻孔照明装置

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